Implantable drug delivery device

ABSTRACT

The invention is directed to an implantable device to enable delivery of drugs to the retina. The device minimizes stress to the retina by virtue of its softness and smooth shape that conform to the retina. Drugs are delivered by osmosis or by the device dissolving. It may be connected to an externally mounted pump and drug reservoir that control the amount of drug. It contains one or more holes that are positioned to deliver drugs to the desired location. Drugs may stimulate the retina to enable vision in blind patients. Drugs may be injected directly inside the eye by a trans-scleral pump and valve drug delivery device.

CROSS REFERENCE TO RELATED APPLICATION

This application is a continuation-in-part of U.S. patent applicationSer. No. 09/783,236, filed on Feb. 13, 2001, entitled “IMPLANTABLERETINAL ELECTRODE ARRAY CONFIGURATION FOR MINIMAL RETINAL DAMAGE ANDMETHOD OF REDUCING RETINAL STRESS.”

FEDERALLY SPONSORED RESEARCH

This invention was made with government support under grant No.

R24EY12893-01, awarded by the National Institutes of Health. Thegovernment has certain rights in the invention.

FIELD OF THE INVENTION

This invention relates to a device and methods and more particularly toa controlled time of release and rate of release, drug delivery device,which may be implanted in a living body.

BACKGROUND OF THE INVENTION

In 1755, LeRoy passed the discharge of a Leyden jar through the orbit ofa man who was blind from cataract and the patient saw “flames passingrapidly downwards.” Ever since, there has been a fascination withelectrically elicited visual perception. The general concepts ofelectrical stimulation of retinal cells to produce these flashes oflight or phosphenes has been known for quite some time. Based on thesegeneral principles, some early attempts at devising a prosthesis foraiding the visually impaired have included attaching electrodes to thehead or eyelids of patients. While some of these early attempts met withsome limited success, these early prosthesis devices were large, bulkyand could not produce adequate simulated vision to truly aid thevisually impaired.

In the early 1930's, Foerster investigated the effect of electricallystimulating the exposed occipital pole of one cerebral hemisphere. Hefound that, when a point at the extreme occipital pole was stimulated,the patient perceived a small spot of light directly in front andmotionless (a phosphene). Subsequently, Brindley and Lewin (1968)thoroughly studied electrical stimulation of the human occipital cortex.By varying the stimulation parameters, these investigators described indetail the location of the phosphenes produced relative to the specificregion of the occipital cortex stimulated. These experimentsdemonstrated: (1) the consistent shape and position of phosphenes; (2)that increased stimulation pulse duration made phosphenes brighter; and(3) that there was no detectable interaction between neighboringelectrodes which were as close as 2.4 mm apart.

As intraocular surgical techniques have advanced, it has become possibleto apply stimulation on small groups and even on individual retinalcells to generate focused phosphenes through devices implanted withinthe eye itself. This has sparked renewed interest in developing methodsand apparati to aid the visually impaired. Specifically, great efforthas been expended in the area of intraocular retinal prosthesis devicesin an effort to restore vision in cases where blindness is caused byphotoreceptor degenerative retinal diseases such as retinitis pigmentosaand age related macular degeneration which affect millions of peopleworldwide.

Neural tissue can be artificially stimulated and activated by prostheticdevices that pass pulses of electrical current through electrodes onsuch a device. The passage of current causes changes in electricalpotentials across neuronal membranes, which can initiate neuron actionpotentials, which are the means of information transfer in the nervoussystem.

Based on this mechanism, it is possible to input information into thenervous system by coding the information as a sequence of electricalpulses which are relayed to the nervous system via the prostheticdevice. In this way, it is possible to provide artificial sensationsincluding vision.

One typical application of neural tissue stimulation is in therehabilitation of the blind. Some forms of blindness involve selectiveloss of the light sensitive transducers of the retina. Other retinalneurons remain viable, however, and may be activated in the mannerdescribed above by placement of a prosthetic electrode device on theinner (toward the vitreous) retinal surface. This placement must bemechanically stable, minimize the distance between the device electrodesand the neurons, and avoid undue compression of the neurons.

In 1986, Bullara (U.S. Pat. No. 4,573,481) patented an electrodeassembly for surgical implantation on a nerve. The matrix was siliconewith embedded iridium electrodes. The assembly fit around a nerve tostimulate it.

Dawson and Radtke stimulated cat's retina by direct electricalstimulation of the retinal ganglion cell layer. These experimentersplaced nine and then fourteen electrodes upon the inner retinal layer(i.e., primarily the ganglion cell layer) of two cats. Their experimentssuggested that electrical stimulation of the retina with 30 to 100 μAcurrent resulted in visual cortical responses. These experiments werecarried out with needle-shaped electrodes that penetrated the surface ofthe retina (see also U.S. Pat. No. 4,628,933 to Michelson).

The Michelson '933 apparatus includes an array of photosensitive deviceson its surface that are connected to a plurality of electrodespositioned on the opposite surface of the device to stimulate theretina. These electrodes are disposed to form an array similar to a “bedof nails” having conductors which impinge directly on the retina tostimulate the retinal cells. Such a device increases the possibility ofretinal trauma by the use of its “bed of nails” type electrodes thatimpinge directly on the retinal tissue.

The art of implanting an intraocular prosthetic device to electricallystimulate the retina was advanced with the introduction of retinal tacksin retinal surgery. De Juan, et al. at Duke University Eye Centerinserted retinal tacks into retinas in an effort to reattach retinasthat had detached from the underlying choroid, which is the source ofblood supply for the outer retina and thus the photoreceptors. See,e.g., E. de Juan, et al., 99 Am. J. Ophthalmol. 272 (1985). Theseretinal tacks have proved to be biocompatible and remain embedded in theretina, and choroid/sclera, effectively pinning the retina against thechoroid and the posterior aspects of the globe. Retinal tacks are oneway to attach a retinal array to the retina.

The retina is extraordinarily fragile. In particular, retinal neuronsare extremely sensitive to pressure; they will die if even a modestintraocular pressure is maintained for a prolonged period of time.Glaucoma, which is one of the leading causes of blindness in the world,can result from a chronic increase of intraocular pressure of only 10 mmHg. Furthermore, the retina, if it is perforated or pulled, will tend toseparate from the underlying epithelium, which will eventually render itfunctionless. Thus attachment of a conventional prosthetic retinalelectrode device carries with it the risk of damage to the retina,because of the pressure that such a device could exert on the retina.

Byers, et al. received U.S. Pat. No. 4,969,468 in 1990 that disclosed a“bed of nails” electrode array that in combination with processingcircuitry amplifies and analyzes the signal received from the tissueand/or which generates signals that are sent to the target tissue. Thepenetrating electrodes are damaging to the delicate retinal tissue of ahuman eye and therefore are not applicable to enabling sight in theblind.

In 1992, U.S. Pat. No. 5,109,844 issued to de Juan, et al. on a methodof stimulating the retina to enable sight in the blind wherein a voltagestimulates electrodes that are in close proximity to the retinalganglion cells. A planar ganglion cell-stimulating electrode ispositioned on or above the retinal basement membrane to enabletransmission of sight-creating stimuli to the retina. The electrode is aflat array containing 64 electrodes.

Norman, et al. received U.S. Pat. No. 5,215,088 in 1993 on athree-dimensional electrode device as a cortical implant for visionprosthesis. The device contains perhaps a hundred small pillars each ofwhich penetrates the visual cortex in order to interface with neuronsmore effectively. The array is strong and rigid and may be made of glassand a semiconductor material.

U.S. Pat. No. 5,476,494, issued to Edell, et al. in 1995, describes aretinal array held gently against the retina by a cantilever, where thecantilever is anchored some distance from the array. Thus, the anchorpoint is removed from the area served by the array. This cantileverconfiguration introduces complexity and it is very difficult to controlthe restoring force of the cantilever due to varying eye sizes, whichthe instant invention avoids.

Sugihara, et al. received U.S. Pat. No. 5,810,725 in 1998 on a planarelectrode to enable stimulation and recording of nerve cells. Theelectrode is made of a rigid glass substrate. The lead wires whichcontact the electrodes are indium tin oxide covered with a conductingmetal and coated with platinum containing metal. The electrodes areindium tin oxide or a highly electrically conductive metal. Severallead-wire insulating materials are disclosed including resins.

U.S. Pat. No. 5,935,155, issued to Humayun, et al. in 1999, describes avisual prosthesis and method of using it. The Humayun patent includes acamera, signal processing electronics and a retinal electrode array. Theretinal array is mounted inside the eye using tacks, magnets, oradhesives. Portions of the remaining parts may be mounted outside theeye. The Humayun patent describes attaching the array to the retinausing retinal tacks and/or magnets. This patent does not addressreduction of damage to the retina and surrounding tissue or problemscaused by excessive pressure between the retinal electrode array and theretina.

Mortimer's U.S. Pat. No. 5,987,361 disclosed a flexible metal foilstructure containing a series of precisely positioned holes that in turndefine electrodes for neural stimulation of nerves with cuff electrodes.Silicone rubber may be used as the polymeric base layer. This electrodeis for going around nerve bundles and not for planar stimulation.

An alternative approach to stimulating the retina with electricalstimulation is the stimulation of the retinal nerves with drugs.

Various drugs have been developed to assist in the treatment of a widevariety of ailments and diseases. However, in many instances such drugsare not capable of being administered either orally or intravenouslywithout the risk of various detrimental side effects. Systems foradministering such drugs have been developed, many of which provide arelease rate that reduces the occurrence of detrimental side effects.For example, intravenous ganciclovir (GCV) is effective in the treatmentof CMV retinitis in AIDS patients, but bone marrow toxicity limits itsusefulness. It is further limited by the risk of sepsis related topermanent indwelling catheters and the inability to receive concurrenttherapy with zidovudine (AZT).

One approach utilizes implantable microfluidic delivery systems, as themicrochip drug delivery devices of Santini, et al. (U.S. Pat. No.6,123,861) and Santini, et al. (U.S. Pat. No. 5,797,898) or fluidsampling devices, must be impermeable and they must be biocompatible.Greenberg, et al. in U.S. patent application Ser. No. 10/046458 andGreenberg, et al. in U.S. patent application Ser. No. 10/096,183 presentnovel implantable microfluidic delivery systems for drugs and othermaterials, both of which are incorporated herein by reference in theirentirety. The devices must not only exhibit the ability to resist theaggressive environment present in the body, but must also be compatiblewith both the living tissue and with the other materials of constructionfor the device itself. The materials are selected to avoid both galvanicand electrolytic corrosion.

In microchip drug delivery devices, the microchips control both the rateand time of release of multiple chemical substances and they control therelease of a wide variety of molecules in either a continuous or apulsed manner. A material that is impermeable to the drugs or othermolecules to be delivered and that is impermeable to the surroundingfluids is used as the substrate. Reservoirs are etched into thesubstrate using either chemical etching or ion beam etching techniquesthat are well known in the field of microfabrication. Hundreds tothousands of reservoirs can be fabricated on a single microchip usingthese techniques.

The physical properties of the release system control the rate ofrelease of the molecules, e.g., whether the drug is in a gel or apolymer form. The reservoirs may contain multiple drugs or othermolecules in variable dosages. The filled reservoirs can be capped withmaterials either that degrade or that allow the molecules to diffusepassively out of the reservoir over time. They may be capped withmaterials that disintegrate upon application of an electric potential.Release from an active device can be controlled by a preprogrammedmicroprocessor, remote control, or by biosensor. Valves and pumps mayalso be used to control the release of the molecules.

A reservoir cap can enable passive timed release of molecules withoutrequiring a power source, if the reservoir cap is made of materials thatdegrade or dissolve at a known rate or have a known permeability. Thedegradation, dissolution or diffusion characteristics of the capmaterial determine the time when release begins and perhaps the releaserate.

Alternatively, the reservoir cap may enable active timed release ofmolecules, requiring a power source. In this case, the reservoir capconsists of a thin film of conductive material that is deposited overthe reservoir, patterned to a desired geometry, and serves as an anode.Cathodes are also fabricated on the device with their size and placementdetermined by the device's application and method of electricalpotential control. Known conductive materials that are capable of use inactive timed-release devices that dissolve into solution or form solublecompounds or ions upon the application of an electric potential,including metals, such as copper, gold, silver, and zinc and somepolymers.

When an electric potential is applied between an anode and cathode, theconductive material of the anode covering the reservoir oxidizes to formsoluble compounds or ions that dissolve into solution, exposing themolecules to be delivered to the surrounding fluids. Alternatively, theapplication of an electric potential can be used to create changes inlocal pH near the anode reservoir cap to allow normally insoluble ionsor oxidation products to become soluble. This allows the reservoir capto dissolve and to expose the molecules to be released to thesurrounding fluids. In either case, the molecules to be delivered arereleased into the surrounding fluids by diffusion out of or bydegradation or dissolution of the release system. The frequency ofrelease is controlled by incorporation of a miniaturized power sourceand microprocessor onto the microchip.

One solution to achieving biocompatibility, impermeability, and galvanicand electrolytic compatibility for an implanted device is to encase thedevice in a protective environment. It is well known to encaseimplantable devices with glass or with a case of ceramic or metal.Schulman, et al. (U.S. Pat. No. 5,750,926) is one example of thistechnique. It is also known to use alumina as a case material for animplanted device as disclosed in U.S. Pat. No. 4,991,582. Santini, etal. (U.S. Pat. No. 6,123,861) discuss the technique of encapsulating anon-biocompatible material in a biocompatible material, such aspoly(ethylene glycol) or polytetrafluoroethylene-like materials. Theyalso disclose the use of silicon as a strong, non-degradable, easilyetched substrate that is impermeable to the molecules to be deliveredand to the surrounding living tissue. The use of silicon allows thewell-developed fabrication techniques from the electronic microcircuitindustry to be applied to these substrates. It is well known, however,that silicon is dissolved when implanted in living tissue or in salinesolution.

An alternative approach to microfluidic devices is, for example, is anorally administered pill or capsule that contains a drug encapsulatedwithin various layers of a composition that dissolves over a period oftime in the digestive tract, thereby allowing a gradual or slow releaseof the drug into the system.

Another type of device for controlling the administration of such drugsis produced by coating a drug with a polymeric material permeable to thepassage of the drug to obtain the desired effect. Such devices areparticularly suitable for treating a patient at a specific local areawithout having to expose the patient's entire body to the drug. This isadvantageous because any possible side effects of the drug could beminimized.

Such systems are particularly suitable for treating ailments affectingthe eye. Advances for administering a drug to the external surface ofthe eye are disclosed in U.S. Pat. No. 4,014,335 to Arnold. Arnolddescribes various ocular inserts that act as a deposit or drug reservoirfor slowly releasing a drug into the tear film for prolonged periods.These inserts are fabricated of a flexible polymeric material that isbiologically inert, non-allergenic, and insoluble in tear fluid. Toinitiate the therapeutic programs of these devices, the ocular insertsare placed in the cul-de-sac between the sclera of the eyeball and theeyelid for administering the drug to the eye.

Devices formed of polymeric materials that are insoluble in tear fluidretain their shape and integrity during the course of the needed therapyto serve as a drug reservoir for continuously administering a drug tothe eye and the surrounding tissues at a rate that is not effected bydissolution or erosion of the polymeric material. Upon termination ofthe desired therapeutic program, the device is removed from thecul-de-sac.

Another type of device used for sustained release of a drug to theexternal surface of the eye, described in U.S. Pat. No. 3,416,530, ismanufactured with a plurality of capillary openings that communicatebetween the exterior of the device and the interior chamber generallydefined from a polymeric membrane. While these capillary openings inthis construction are effective for releasing certain drugs to the eye,they add considerable complexity to the manufacture of the devicebecause it is difficult to control the size of these openings inlarge-scale manufacturing using various polymers.

Another device, described in U.S. Pat. No. 3,618,604, does not involvesuch capillary openings, but instead provides for the release of thedrug by diffusion through a polymeric membrane. The device, in apreferred embodiment, as disclosed in that patent, comprises a sealedcontainer having the drug in an interior chamber. Nonetheless, asdescribed in U.S. Pat. No. 4,014,335, certain problems have beenidentified with such devices such as the difficult task of sealing themargins of the membrane to form the container. In addition, stresses andstrains introduced into the membrane walls from deformation duringmanufacturing of those devices may cause the reservoir to rupture andleak.

Another such device, described in U.S. Pat. No. 4,014,335, comprises athree-layered laminant having a pair of separate and discrete first andthird walls formed of a material insoluble in tear fluid with one of thewalls formed of a drug release material permeable to the passage of drugand the other wall formed of a material impermeable to the passage ofthe drug.

Smith, U.S. Pat. No. 5,378,475, discusses sustained release drugdelivery devices for selected areas wherein release of the drug isallowed to pass through the device in a controlled manner by usingpermeable coatings. Parel, U.S. Pat. No. 5,098,443, describes methods ofimplanting intraocular and intraorbital devices for controlled releaseof drugs as a polymer biodegrades or as the implant releases the drug byosmosis.

The above described systems and devices are intended to providesustained release of drugs effective in treating patients at a desiredlocal or systemic level for obtaining certain physiological orpharmacological effects. However, there are many disadvantagesassociated with their use including the fact that it is often difficultto obtain the desired release rate of the drug. The need for a betterrelease system is especially significant in the treatment of CMVretinitus.

Further situations that would benefit from an improved drug deliverydevice for interior of an eye include neurotrophic factors,anti-inflammatory, anti-angiogenic (e.g., anti-vegf ) anti-viral,anti-bacterial, and anti-neoplastic (i.e., anti cancer) drugs. Thesevarious treatments would benefit blindness, caused for example by outerretinal blindness, glaucoma, macular degeneration, diabeticretinopthaly, and reininitis uveitis, to name a few. Thus, there remainsa long-felt need in the art for an improved system for providingsustained release of a drug to a patient to obtain a desired local orsystemic physiological or pharmacological effect. In addition, all ofthese devices release their drug into the tear film. If relatively highlevels are required inside the eye, such devices are ineffective.

OBJECTS OF THE INVENTION

It is an object of the invention to attach an electrode array body tothe retina of an eye and enable blind people to see images.

It is an object of the invention to attach an electrode array body tothe retina while avoiding or minimizing harmful stresses on the retinafrom the electrode array body.

It is an object of the invention to enable a surgeon to easily locatethe mounting aperture for attachment of an electrode array body to theretina of an eye by a surgical tack.

It is an object of the invention to provide tabs for attachment of theelectronics and feeder cable to the recipient of the retinal electrodearray.

It is an object of the invention to provide drugs to the interior of aneye by an implanted device.

It is an object of the invention to enable vision by stimulating theretina with drugs that are injected on the retina with an implanteddevice.

Other objects, advantages and novel features of the present inventionwill become apparent from the following detailed description of theinvention when considered in conjunction with the accompanying drawing.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a perspective view of the retinal electrode arrayassembly showing the electrodes and signal conductors as well asmounting aperture for tacking the assembly inside the eye, wherein boththe array and its associated electronics are located inside the eye.

FIG. 2 illustrates a perspective view of the retinal electrode arrayassembly showing the electrodes and signal conductors as well asmounting aperture for tacking the assembly inside the eye, wherein theassociated electronics are located outside the eye.

FIG. 3 illustrates a perspective view of the retinal electrode arrayassembly wherein the array is installed inside the eye and theassociated electronics are installed outside the eye at some distancefrom the sclera wherein the feeder cable contains both a coiled cableleading between the electronics and the sclera and a series of fixationtabs along the feeder cable for securing the feeder cable by suture.

FIG. 4 depicts a cross-sectional view of the retinal electrode array,the sclera, the retina and the retinal electrode array showing theelectrodes in contact with the retina.

FIG. 5 depicts a cross-sectional view of the retinal electrode arrayshowing a strain relief slot, strain relief internal tab and a mountingaperture through a reinforcing ring for a mounting tack to hold thearray in position.

FIG. 6 illustrates a cross-sectional view of the retinal electrode arrayshowing a strain relief slot and a ferromagnetic keeper to hold thearray in position.

FIG. 7 illustrates a cross-sectional view of the retinal electrode arrayshowing a strain relief slot and a mounting aperture through areinforcing ring for a mounting tack to hold the array in position,wherein the strain relief internal tab containing the mounting apertureis thinner than the rest of the array.

FIG. 8 illustrates a cross-sectional view of an eye showing an arraybody attached to a retina.

FIG. 9 illustrates a cross-sectional view of an eye showing an arraybody with external reservoir.

FIG. 10 illustrates a perspective view of an array body.

FIG. 11 illustrates a perspective view of an array body with an attachedreservoir.

FIG. 12 illustrates a perspective view of a multi-reservoir array bodywith an attached reservoir.

FIG. 13 illustrates a cross-sectional view of an eye showing a drugdelivery system.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The following description is the best mode presently contemplated forcarrying out the invention. This description is not to be taken in alimiting sense, but is made merely for describing the general principlesof the invention. The scope of the invention should be determined withreference to the claims.

FIG. 1 provides a perspective view of a preferred embodiment of theretinal electrode array, generally designated 2, comprising oval-shapedelectrode array body 4, a plurality of electrodes 6 made of a conductivematerial, such as platinum or one of its alloys, but that can be made ofany conductive biocompatible material such as iridium, iridium oxide ortitanium nitride, and single reference electrode 6A made of the samematerial as electrode 6, wherein the electrodes are individuallyattached to separate conductors 8 made of a conductive material, such asplatinum or one of its alloys, but which could be made of anybiocompatible conductive material, that is enveloped within aninsulating sheath 10, that is preferably silicone, that carries anelectrical signal to each of the electrodes 6. “Oval-shaped” electrodearray body means that the body may approximate either a square or arectangle shape, but where the corners are rounded. The referenceelectrode 6A is not necessarily stimulated, but is attached to aconductor, as are electrodes 6. The electrodes could be used in anotherapplication as sensors to transmit electrical signals from a nerve. Theelectrodes 6 transmit an electrical signal to the eye while referenceelectrode 6A may be used as a ground, reference, or control voltage.

Electrode array body 4 is made of a soft material that is compatiblewith the body. In a preferred embodiment, array body 4 is made ofsilicone having a hardness of about 50 or less on the Shore A scale asmeasured with a durometer. In an alternate embodiment, the hardness isabout 25 or less on the Shore A scale as measured with a durometer. Itis a substantial goal to have electrode array body 4 in intimate contactwith the retina of the eye.

Strain relief internal tab 12, defined by a strain relief slot 13 thatpasses through the array body 4, contains a mounting aperture 16 forfixation of the electrode array body 4 to the retina of the eye by useof a surgical tack, although alternate means of attachment such as glueor magnets may be used. Reinforcing ring 14 is colored and opaque tofacilitate locating mounting aperture 16 during surgery and may be madeof tougher material, such as high toughness silicone, than the body ofthe electrode array body to guard against tearing.

Signal conductors 8 are located in an insulated flexible feeder cable 18carrying electrical impulses from the electronics 20 to the electrodes6, although the electrodes can be sensors that carry a signal back tothe electronics. Signal conductors 8 can be wires, as shown, or in analternative embodiment, a thin electrically conductive film, such asplatinum, deposited by sputtering or an alternative thin film depositionmethod. In a preferred embodiment, the entire retinal electrode array 2including the feeder cable 18 and electronics 6 are all implanted insidethe eye. Electronics 20 may be fixated inside the eye to the sclera bysutures or staples that pass through fixation tabs 24. The conductorsare covered with silicone insulation.

Grasping handle 46 is located on the surface of electrode array body 4to enable its placement by a surgeon using forceps or by placing asurgical tool into the hole formed by grasping handle 46. Graspinghandle 46 avoids damage to the electrode body that might be caused bythe surgeon grasping the electrode body directly. Grasping handle 46also minimizes trauma and stress-related damage to the eye duringsurgical implantation by providing the surgeon a convenient method ofmanipulating electrode array body 4.

Grasping handle 46 is made of silicone having a hardness of about 50 onthe Shore A scale as measured with a durometer. A preferred embodimentof the electrode array body 4 is made of a very soft silicone havinghardness of 50 or less on the Shore A scale as measured with adurometer. The reinforcing ring 14 is made of opaque silicone having ahardness of 50 on the Shore A scale as measured with a durometer.

FIG. 2 provides a perspective view of the retinal electrode array 2wherein the electrode array body 4 is implanted inside the eye and theelectronics 20 are placed outside the eye with the feeder cable 18passing through sclera 30. In this embodiment, electronics 38 areattached by fixation tabs 24 outside the eye to sclera 30.

FIG. 3 provides a perspective view of retinal electrode array 2 whereinelectrode array body 4 is implanted on the retina inside the eye andelectronics 38 are placed outside the eye some distance from sclera 30wherein feeder cable 18 contains sheathed conductors 10 assilicone-filled coiled cable 22 for stress relief and flexibilitybetween electronics 38 and electrode array body 4. Feeder cable 18passes through sclera 30 and contains a series of fixation tabs 24outside the eye and along feeder cable 18 for feeder cable 18 to sclera30 or elsewhere on the recipient subject.

FIG. 4 provides a cross-sectional view of electrode array body 4 inintimate contact with retina 32. The surface of electrode array body 4in contact with retina 32 is a curved surface 28 substantiallyconforming to the spherical curvature of retina 32 to minimize stressconcentrations therein. Further, the decreasing radius of sphericalcurvature of electrode array body 4 near its edge forms edge relief 36that causes the edges of array body 4 to lift off the surface of retina32 eliminating stress concentrations. The edge of electrode array body 4has a rounded edge 34 eliminating stress and cutting of retina 32. Theaxis of feeder cable 18 is at right angles to the plane of thiscross-sectional view. Feeder cable 18 is covered with silicone.

FIG. 5 provides a cross-sectional view of electrode array body 4 showingspherically curved surface 28, strain relief slot 13 and mountingaperture 16 through which a tack passes to hold array body 4 in intimatecontact with the eye. Mounting aperture 16 is located in the center ofreinforcing ring 14 that is opaque and colored differently from theremainder of array body 4, making mounting aperture 16 visible to thesurgeon. Reinforcing ring 14 is made of a strong material such as toughsilicone, which also resists tearing during and after surgery. Strainrelief slot 13 forms strain relief internal tab 12 in which reinforcingring 14 is located. Stresses that would otherwise arise in the eye fromtacking array body 4 to the eye through mounting aperture 16 arerelieved by virtue of the tack being located on strain relief internaltab 12.

FIG. 6 provides a cross-sectional view of a preferred embodiment ofelectrode array body 4 showing ferromagnetic keeper 40 that holdselectrode array body 4 in position against the retina by virtue of anattractive force between ferromagnetic keeper 40 and a magnet located onand attached to the eye.

FIG. 7 is a cross-sectional view of the electrode array body 4 whereininternal tab 12 is thinner than the rest of electrode array body 4,making this section more flexible and less likely to transmit attachmentinduced stresses to the retina. This embodiment allows greater pressurebetween array body 4 and the retina at the point of attachment, and alesser pressure at other locations on array body 4, thus reducing stressconcentrations and irritation and damage to the retina.

A significant feature of this drug delivery device is that the drugdelivery device is located out of the field of vision and does not blocklight that is passing from the lens to the retina. Further, the deviceis securedly mounted to the retina at a desired location withoutdamaging the retina. Further, a preferred embodiment is presented inFIG. 8, which provides a cross-section through an eye 101 of a passivedrug-delivery device, wherein the lens 131 and retina 132 are indicated.The drug-containing pillow 107 is preferably securedly attached to theretina 132 by tack 103.

In alternate embodiments, the drug-containing pillow 107 may be locatedelsewhere in the living body, such as in an ear or attached to aneardrum.

In accordance with a significant feature of this preferred embodiment,the pillow 107 may be formed from biodegradable materials, such aspolymers, to release a drug as the material, preferably a polymer,biodegrades. In an alternative embodiment, the pillow 107 may be in theform of a hollow flexible polymeric cocoon with the drug disposedtherewithin for slow release by osmosis. As a further alternativeembodiment, the drug may be embedded in the body of the pillow 107, suchthat the drug is slowly released by osmosis while leaving the pillow 107substantially intact, such that the pillow 107 may be removedsurgically. Attachment of the drug-containing pillow 107 to the retinahas the significant benefit of placing controlled and concentratedamounts of drugs precisely where they are needed to optimize thetherapeutic benefit. The physical shape of pillow 107 and its method ofattachment are optimized to eliminate or minimize physical stress on theretina and the associated eye structures to avoid permanent damage tothe eye.

In contrast to the passive drug delivery device of FIG. 8, and inaccordance with a further preferred embodiment of the present invention,FIG. 9 provides a cross-section through an eye 101, as previouslypresented in FIG. 8, with an active drug delivery device 109 preferablysecuredly attached by tack 103 to the retina 132. Delivery device 109receives drugs from reservoir 111. The drugs are transferred by pressuredevelopment device 115 through feeder tube 118. The flow rate ispreferably controlled in part by micro-valve 105, which is locatedexternal to the eye, and is preferably co-located outside the eye withthe reservoir 111 and pressure development device 115. The reservoir111, pressure development device 115 and valve 105 are preferablyattached to the sclera on the outside of the eye, preferably under theconjunctiva, to enable repair, replacement, and/or refilling the drugdelivery device.

In an alternate embodiment, drug delivery device 109 may be locatedelsewhere in the living body, such as in an ear or on an eardrum.

FIG. 10 provides a perspective view of a preferred embodiment of thepillow, generally designated 107, and previously presented in FIG. 8comprising oval-shaped pillow 107. “Oval-shaped” pillow 107 means thatthe body may approximate either a square or a rectangle shape, but wherethe corners are rounded, as with rounded edge 134.

Pillow 107 is made of a soft material that is compatible with the body.In a preferred embodiment, pillow 107 is made of a polymer having ahardness of about 50 or less on the Shore A scale, as measured with adurometer. In an alternate embodiment, the hardness is about 25 or lesson the Shore A scale, as measured with a durometer. It is a substantialgoal to have pillow 107 in intimate contact with the retina 132 of theeye.

Strain relief internal tab 112, defined by a strain relief slot 113 thatpasses through the pillow 107, contains a mounting aperture 116 forfixation of the pillow 107 to the retina 132 of the eye by use of asurgical tack 103, although alternate means of attachment such as glueor magnets may be used. Reinforcing ring 114 is colored and opaque tofacilitate locating mounting aperture 116 during surgery and may be madeof tougher material, such as high toughness polymer, than the body ofthe pillow 107, to guard against tearing.

Grasping handle 146 is located on the surface of pillow 107 to enableits placement by a surgeon using forceps or by placing a surgical toolinto the hole formed by grasping handle 146. Grasping handle 146 avoidsdamage to the pillow 107 that might be caused by the surgeon graspingthe body directly. Grasping handle 146 also minimizes trauma andstress-related damage to the eye during surgical implantation byproviding the surgeon a convenient method of manipulating pillow 107.Grasping handle 146 is preferably made of a material, such as a polymer,having a hardness of about 50 on the Shore A scale, as measured with adurometer.

FIG. 11 provides a perspective view of a preferred embodiment of thepresent invention, as previously presented in FIG. 9, comprisingdelivery device 109 that is connected by feeder tube 118 to drugreservoir 111 and pressure development device 115. It is obvious thatpressure development device 115 may equally well be replaced by any of anumber of known methods of delivering a fluid from the reservoir 111 andalong the tube 118. As previously discussed, the reservoir 111 ispreferably mounted outside the eye to the sclera, preferably under theconjunctiva, by fixation tabs 124. The feeder tube 118 passes through anincision in the sclera 130. In accordance with a significant feature ofthis preferred embodiment, a micro-valve 105 is located in feeder tube118 outside the eye. Together with pressure development device 115,preferably a micro-pump, this valve 105 controls the flow of drugs tothe delivery device 109.

In a preferred environment, feeder tube 118 branches into a plurality oftubes 110 in delivery device 109. Each tube 110 then creates a capillaryopening 140 where it breaches the surface of delivery device 109. WhileFIG. 11 shows the capillary openings 140 located on the top, bottom andsides of delivery device 109, it is obvious that the tubes may be placedwhere desired in order to maximize the benefit of the drug. In anexemplary design, therefore, all of the capillary openings 140 arelocated on the bottom of delivery device 109, for example, when it isdesirable to deliver the drug to a local point on the retina. In afurther exemplary design, only one capillary opening 140 may be locatedto place the drug at a single location on the retina, for example.

A significant feature of this preferred embodiment is that with anexternally mounted reservoir 111 the reservoir 111 may be refilled byinjecting additional drug into refill aperture 117.

In accordance with a further significant feature of a preferredembodiment of this invention, the stresses that are generated whendelivery device 109 contacts the retina are minimized, as previouslydiscussed, by using an oval shaped design with stress concentrationseliminated or minimized by using soft polymers and rounded edges. Forexample, the “oval-shaped” delivery device 109 means that the body mayapproximate either a square or a rectangle shape, but where deliverydevice 109 is comprised of rounded edges 134.

Delivery device 109 is made of a soft material that is compatible withthe body. In a preferred embodiment, delivery device 109 is made of apolymer having a hardness of about 50 or less on the Shore A scale, asmeasured with a durometer. In an alternate embodiment, the hardness isabout 25 or less on the Shore A scale, as measured with a durometer. Itis a substantial goal to have delivery device 109 in intimate contactwith the retina 132 of the eye.

Strain relief internal tab 112, defined by a strain relief slot 113 thatpasses through the delivery device 109, contains a mounting aperture 116for fixation of the delivery device 109 to the retina 132 of the eye byuse of a surgical tack 103, although alternate means of attachment suchas glue or magnets may be used. Reinforcing ring 114 is colored andopaque to facilitate locating mounting aperture 116 during surgery, andmay be made of tougher material, such as high toughness polymer, thanthe body of the delivery device 109, to guard against tearing.

Grasping handle 146 is located on the surface of delivery device 109 toenable its placement by a surgeon using forceps or by placing a surgicaltool into the hole formed by grasping handle 146. Grasping handle 146avoids damage to the delivery device 109 that might be caused by thesurgeon grasping the body directly. Grasping handle 146 also minimizestrauma and stress-related damage to the eye during surgical implantationby providing the surgeon a convenient method of manipulating pillow 107.Grasping handle 146 is made of a polymer having a hardness of about 50on the Shore A scale, as measured with a durometer.

FIG. 12 provides a perspective view of a preferred embodiment of thepresent invention comprising delivery device 109 that is connected byfeeder tube 118 to drug reservoir 111 and pressure development device115. It is obvious that pressure development device 115 may equally wellbe replaced by any of a number of known methods of delivering a fluidfrom the reservoir 111 and along the tube 118. The reservoir 111 ispreferably mounted outside the eye to the sclera by fixation tabs 124.The feeder tube 118 passes through an incision in the sclera 130.

In accordance with a significant feature of this preferred embodiment,at least one micro-valve 144 is located in each feeder tube 118.Preferably, the micro-valve is located near capillary opening 140, whichis in delivery device 109. Together with pressure development device115, the valves 144 control the flow of drugs. Each micro-valve 144 isconnected to a control wire 162 that in turn is connected to acontroller 160. It is preferred that only one wire or set of wires beutilized to control the micro-valves 144, if more than one micro-valve144 controlled capillary opening 140 is present. In this multiplexcontrol scheme, digital signals from controller 160 control eachmicro-valve 144 independently of all other micro-valves 144. In apreferred embodiment, controller 160 is located external to the eye nearreservoir 111.

In a preferred environment, feeder tube 118 branches into a plurality oftubes 110 in delivery device 109. Each tube 110 then creates a capillaryopening 140 where it breaches the surface of delivery device 109. WhileFIG. 12 shows the capillary openings 140 located on the top, bottom andsides of delivery device 109, it is obvious that the tubes may be placedwhere desired in order to maximize the benefit of the drug.

A further alternative embodiment, not fully illustrated but a variant ofrepresentation of FIG. 12, places the tubes 110 and their capillaryopenings 140 in a preferably symmetrical array located between graspinghandle 146 and aperture 116. An exemplary array is an equidistance 4×4array, wherein the sixteen capillary openings 140 are all located on thecurved surface 128, such that the neurotransmitter drug is releasedadjacent to the retina. One known example of such a drug includesglutamate. There may be a plurality of different drugs used to stimulatethe eye in order to achieve vision, and that each drug may be associatedwith an independent reservoir 111 and tube 110 which in turn has anindependent capillary opening 140. This use of multiple drugs, notillustrated, would enable the retina to be stimulated to achieve colorvision, for example, by the controlled use of independentcolor-stimulating drugs or mixtures of drugs.

In an alternate embodiment, the neurotransmitter drug may be deliveredto neural tissue to stimulate vision, when delivery device 109 is placedon select neural tissue instead of on the retina of an eye.

A further alternative embodiment is represented in FIG. 13, where theeye 201 is shown in cross-section and the lens 231 and retina 232 aredelineated. The drug or drugs to be delivered are contained inexternally mounted reservoir 211, which is preferably located near apressure delivery source, such as the pressure development device 215,which may be a micro-pump, for example. The reservoir 211 can berefilled through refill aperture 217 by injection, for example. Apreferred material for the refill aperture 217 is silicone. Amicro-valve 205 is controlled by a controller to allow the drug to passalong feeder tube 218. Feeder tube 218 passes through an incision in thesclera 230 and terminates in a preferred location within eye 201. Apreferred location for the incision is in the pars plana 244.

The preferred location for terminating the feeder tube 218 for drugdelivery may be in the vitreous 242 or in the anterior chamber 240. Ifin the anterior chamber 240, the feeder tube 218 looks much like aglaucoma drain, for example. Drugs may be delivered in controlled dosesto the precise area of the eye 201 desired to optimize the therapeuticeffect of treatment with minimal drug usage.

Obviously, many modifications and variations of the present inventionare possible in light of the above teachings. It is therefore to beunderstood that within the scope of the appended claims, the inventionmay be practiced otherwise than as specifically described.

1. An implantable device for drug delivery comprising: a biodegradablebody being comprised of at least one mounting aperture in saidbiodegradable body that is suitable for attaching said biodegradablebody to a retina with a tack; said body having a generally oval shapesuitable to be placed adjacent to the plane of a retina, said ovalshaoed body being curved such that it substantially conforms to thespherical curvature of at least portion of a recipient's eye.
 2. Theimplantable device for drug delivery according to claim 1 wherein saidbiodegradable body further comprises a strain relief internal tab thatis defined by a strain relief slot partially surrounding said mountingaperture.
 3. The implantable device for drug delivery according to claim2 wherein said strain relief internal tab is thinner than the rest ofthe biodegradable body, thereby reducing stress in the retina fromattachment of said biodegradable body.
 4. An implantable device for drugdelivery comprising: a biodegradable body being comprised of materialhaving a hardness of about 50 or less on the Shore A scale as measuredwith a durometer; said body having a generally oval shape suitable to beplaced adjacent to the plane of a retina, said oval shaped body beingcurved such that it substantially conforms to the spherical curvature ofat least portion of a recipient's eve.
 5. An implantable device for drugdelivery comprising: a biologically inert hollow body defining at leastone void, and wherein said inert body is comprised of material having ahardness of about 50 or less on the Shore A scale as measured with adurometer; said void containing at least one drug: said hollow bodyhaving a generally oval shape, said oval shaped body being curved suchthat it substantially conforms to the spherical curvature of at least aportion of a recipient's eye.
 6. An implantable device for drug deliverycomprising: a biologically inert body having a first side, an edge, anda second side, wherein said inert body is comprised of material having ahardness of about 50 or less on the Shore A scale as measured with adurometer; a first flexible layer on said first side of said inert body;said first flexible layer defining at least one mounting aperture.
 7. Animplantable device for drug delivery to enable vision comprising: abiologically inert body having a first side, an edge, and a second side;a first flexible aver on said first side of said inert body suitable tocontact neural tissue; said first flexible layer defining at least onedelivery aperture; a second flexible layer on said second side; a thirdflexible layer on said edge; a drug delivery device delivering at leastone drug to said at least one delivery aperture, wherein said at leastone drug is composed of glutamate.
 8. An implantable device for drugdelivery to enable vision comprising: a biologically inert body having afirst side, an edge, and a second side; a first flexible layer on saidfirst side of said inert body suitable to contact neural tissue; saidfirst flexible layer defining at least one delivery aperture, whereinsaid at least one aperture further comprises an ordered array ofone-hundred apertures in a ten by ten matrix; a second flexible layer onsaid second side; a third flexible layer on said edge; a drug deliverydevice delivering at least one drug to said at least one deliveryaperture.
 9. An implantable device for drug delivery to enable visioncomprising: a biologically inert body having a first side, an edge, anda second side; a first flexible layer on said first side of said inertbody suitable to contact neural tissue; said first flexible layerdefining at least one delivery aperture; a second flexible layer on saidsecond side; a third flexible layer on said edge; a drug delivery devicedelivering at least one drug to said at least one delivery aperture,wherein said drug delivery device is comprised of: a reservoir; apressure development device; at least one feeder tube that is attachedto said inert body.
 10. The implantable device for drug delivery toenable vision according to claim 9 wherein said drug delivery device iscomprised of at least one valve that is located near each of said atleast one aperture to control the delivering of said at least one drug.11. The implantable device for drug delivery to enable vision accordingto claim 9 wherein said drug delivery device is suitable for attachmentto a sclera under a conjunctiva.
 12. An implantable device for drugdelivery to enable vision comprising: a biologically inert body having afirst side, an edge, and a second side, wherein said inert body iscomprised of material having a hardness of about 50 or less on the ShoreA scale as measured with a durometer; a first flexible layer on saidfirst side of said inert body suitable to contact neural tissue; saidfirst flexible layer defining at least one delivery aperture, whereinsaid at least one aperture further comprises an ordered array ofone-hundred apertures in a ten by ten matrix; a second flexible layer onsaid second side; a third flexible layer on said edge; a drug deliverydevice delivering at least one drug to said at least one deliveryaperture.